|Publication number||US7368281 B2|
|Application number||US 10/794,937|
|Publication date||May 6, 2008|
|Filing date||Mar 5, 2004|
|Priority date||Mar 27, 2003|
|Also published as||DE602004021685D1, EP1616169A1, EP1616169B1, US20040191765, WO2005012886A1|
|Publication number||10794937, 794937, US 7368281 B2, US 7368281B2, US-B2-7368281, US7368281 B2, US7368281B2|
|Inventors||Eric J. Mozdy, Frederic J-Y Quan, Po Ki Yuen|
|Original Assignee||Corning Incorporated|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (29), Non-Patent Citations (4), Referenced by (18), Classifications (25), Legal Events (6)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application claims the benefit of U.S. Provisional Application No. 60/458,119 filed Mar. 27, 2003, the contents of which in its entirety is hereby incorporated by reference.
The present invention pertains to evanescent-field detection of biological and chemical agents. More particularly, the invention relates to a sensor system, its associated opto-electronic components, and methods of using the system to monitor real-time biological-binding events or chemical reactions for airborne or fluidic analytes.
Evanescent field-based sensors are fast becoming a technology of choice for accurate label-free detection of biological reactions. In recent years, the biological, pharmaceutical, and other research communities have begun to recognize that evanescent field-based sensors can be useful, high-throughput research tools to measure a variety of biological or biochemical functions. This technology typically involves the use of an optical evanescent field to sense changes in the local environment (refractive index) where a biological or chemical reaction takes place. A grating or prism can be used to couple light in and out of an optical mode, thereby probing the effective index of the mode, which changes together with the surface index. Changes in the angle or wavelength of the probe light, for example, indicate changes of the waveguide effective index that result from activity at the sensor surface. Evanescent field sensors have demonstrated high sensitivity, and an ability to detect binding reactions of as little as about 250 Da molecular weight (e.g., biotin binding to streptavidin). Typical spore-based pathogens (e.g., anthrax) are fairly massive (≧20-50 kDa) entities compared to tiny pharmaceutical drug candidates that are the more traditional target of evanescent technology. As a result, such sensors and instruments should be sufficiently sensitive for airborne pathogen detection. Furthermore, because of their responsiveness to index of refraction, these kinds of sensors also respond to chemicals, and can therefore likewise detect chemical toxins.
The present invention, according to one aspect, relates in part to a sensor system for detecting either liquid- or airborne biological pathogens, chemical agents, and other harmful or toxic species. The sensor system comprises: 1) an evanescent-field sensor comprising a substrate surface having at least in-part a bio- or chemo-responsive layer, which forms a serially renewable sensing region; 2) an optical interrogation apparatus for monitoring the bio- or chemo-responsive layer, the optical interrogation apparatus comprising a light source, an optical delivery system, and a detection instrument; 3) an air-fluid delivery system, comprising either macro or micro-fluidic passages designed to convey biological or chemical analytes to one or more sensing regions. The substrate has reactant and non-reactant regions and can be modified with one or more materials, which enhance stable immobilization of the bio- or chemo-responsive layer. For instance, the bio- or chemo-reactive layer may include a pathogen-specific antibody or ganglioside probe for biological analytes. Alternatively, the bio- or chemo-reactive layer may be designed to adsorb a chemical molecule or moiety of interest, resulting in either a change in mass or refractive index. The change in mass may result from the adherence of the chemical molecule to the surface or a removal of the original chemistry from the sensor surface.
The evanescent-field sensor, according to the invention, has a continuous substrate having thereon at least one, preferably two, or more contiguous sets of either sensor regions or arrays of sensors, wherein each array comprises a predetermined set of multiple regions for biological or chemical sensing. The bio- or chemo-responsive layer in a sensing region is specifically formulated to react with particular biological or chemical analytes. In preferred embodiments, the evanescent-field sensor includes a collection of individual substrates, each having one or more sensing regions that can be optically interrogated either in series or in parallel. Preferably, the substrate is optically transparent. The system preferably also includes a sample collection or concentration unit to concentrate in situ particles in the air before they are drawn into the sensing region.
The sensor system, according to an embodiment, preferably includes a substrate with tensile strength and pliability can be supplied from a dispensing device as a single unit in a continuous fashion; and the substrate is configurable to a fraction of its fully extended length along its longest dimension without breaking, and can be retrieved from such configuration as a continuous body suitable for performing molecular interactive assays with toxin targets. Alternatively, the evanescent-field sensor has a substrate in the form of a revolving platform. According to certain embodiments, the device comprises a collection of individual substrates, each having one or more sensing regions that can be optically interrogated in series.
In another aspect, the present invention pertains to a method for detecting toxins. The method comprises: providing an evanescent-field sensor system like that described above, having at least in-part a bio- or chemo-responsive layer that forms a serially renewable sensing region; exposing an individual sensor array to an environment with unknown hazardous contaminants; and monitoring a response from said sensor system to determine a contamination level. The sensor system may be deployed on a mobile platform, which can be moved to or through the contaminated environment. Sensor response signals can be transmitted to a remote analysis location.
Additional features and advantageous of the present invention will be revealed in the following detailed description. Both the foregoing summary and the following detailed description and examples are merely representative of the invention, and are intended to provide an overview for understanding the invention as claimed.
Before describing the present invention in detail, this invention is not necessarily limited to specific compositions, reagents, process steps, or equipment, as such may vary. As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the context clearly dictates otherwise. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting. All technical and scientific terms used herein have the usual meaning conventionally understood by persons skilled in the art to which this invention pertains, unless context defines otherwise.
The term “air-fluid delivery system” as used herein refers to a fluidic (i.e., gaseous or liquid) system that can collect samples of biological or chemical analytes from the atmosphere or surrounding environs, and deliver the samples to a sensor.
The term “analyte,” “toxin,” or “target” as used herein refers to biological pathogens, chemical agents, and other harmful or toxic species to be detected.
The term “bio-responsive” or “chemo-responsive” as used herein refers to the ability to adsorb, desorb, react with, or bind a biological or chemical species.
The term “bio- or chemo-responsive layer” as used herein refers to a collection of probes on a substrate surface of an evanescent-field sensor.
The term “evanescent” as used herein refers to that portion of an optical field where the effective index of the optical field exceeds the local index of the medium, thereby necessitating an exponentially decaying field in space, according to Maxwell's Equations.
The term “evanescent-field sensor” as used herein refers generally to any kind of sensor where an evanescent optical field interacts with a medium to be sensed, and changes in the optical field can be detected to indicate properties or changing characteristics of the medium.
The term “microspot” as used herein refers to a discrete or defined area, locus, or spot on the surface of a substrate, containing probe material. One or more micropots, as in an array, constitute a sensing region.
The term “probe” as used herein refers to either a natural or synthetic, bio- or chemo-reactive molecule, which has been immobilized to a substrate surface constituting part of a sensing medium. A set of probes can bind or otherwise react with analytes. Examples of probes which may be employed according to this invention may include, but are not limited to, antibodies, (e.g., monoclonal antibodies and antisera reactive with specific antigenic determinants), glycolipids including gangliosides, pharamaceutical or toxin molecules, polynucleotides, peptide nucleic acid (PNA), peptides, proteins, cofactors, lectins, polysaccharides, viruses, cells, cellular or lipid membranes, membrane immuno-receptors, and organelles. For chemical detection, the probes may include a polymer matrix, or a ligand-gated ion channel membrane. Preferably, probes are arranged in a spatially addressable manner to form an array of microspots. When the array is exposed to a sample of interest, molecules in the sample selectively and specifically binds to their binding partners (i.e., probes). The binding of a “target” to the probes occurs to an extent determined by the concentration of that “target” molecule and its affinity for a particular probe.
As used herein, the term “receptor” refers to a molecule that has an affinity for a ligand. Receptors may be naturally-occurring or man-made molecules. They may be employed in their unaltered state or as aggregates with other species. Receptors are sometimes referred to in the art as anti-ligands. A “ligand-receptor pair” is formed when two molecules have combined through molecular recognition to form a complex.
The term “sensing region” as used herein refers to an area or window on a surface of an evanescent-field sensor where analytes may attach and be detected. Over the total surface of an evanescent-field sensor, there is at least one, preferably a plurality of sensing regions that may be each optically accessed in sequence or in parallel. In other words, a sensing region is analogous to a slide or a frame of film.
The term “substrate” or “substrate surface” as used herein refers to a solid or semi-solid material, which can form a stable support and is capable of functioning as an evanescent-field sensor. The substrate surface can be selected from a variety of materials.
The present invention pertains, in part, to a sensor system and method for detecting toxins by means of evanescent-field optics.
According to a second aspect of the invention, the method of using the evanescent-field sensors described above to detect various kinds of species comprises: providing a sensor system having an evanescent-field sensor comprising a substrate surface having at least in-part a bio- or chemo-responsive layer, which forms a serially renewable sensing region, and a continuous substrate having thereon at least two or more contiguous sets of sensor arrays, wherein each array comprises a predetermined set of multiple regions for biological or chemical sensing. An individual sensing region or sensor array may be exposed an environment with unknown hazardous contaminants; and monitoring a response from said sensor system to determine a contamination level.
A. The Sensor
According to the invention, the sensor system provides a multiplexed, high-throughput format for evanescent detection of biological entities, chemical agents, and other harmful pathogenic or toxic species. The sensor system comprises an evanescent-field sensor having a bio- or chemo-responsive layer, which forms part of a sensing region, on at least part of a substrate surface. Each sensing region provides an area or window in which analyte-binding sites, or microspots, on the substrate can be optically interrogated.
In order to render the sensors active for pathogen or toxin detection, either the entire continuous substrate surface or at least parts thereof would be coated with an appropriate biological or chemical species for the desired bio- or chemo-reactivity. In other words, coating the entire substrate with a chemo- or bio-reactive substance is not generally required; only the active microspots of a sensor area need to have a reactive coating. In the instance of multiplexed sensing, each row of separate sensors (along the continuous direction of the substrate) may be distinguished by a different bio- or chemo-reactive coating. In addition, one may also include a control sensor with each array of multiplexed toxin sensors where no reactive coating is employed, in order to distinguish true specific detection from non-specific (background) noise.
The sensing medium on the substrate is a bio- or chemo-reactive layer comprising a variety of ligands or receptor molecules, referred to as probes, which can bind with specificity to fluid- or airborne analytes. To develop a sensor specific to pathogens or toxins probes need to be inmuobilized securely on the surface of the sensor. The surface chemistry in or around a sensing region of the substrate is usually tailored for immobilizing particular kinds of probes. The substrate may comprise at least a binding entity selected from either a biological or chemical molecule, each having a specific affinity for another molecule through either covalent or non-covalent bonding. Preferably, a specific binding entity may contain (either by nature or by modification) a functional chemical group (primary amine, sulfhydryl, aldehyde, carboxylic, acrylic, etc.), a common sequence (nucleic acids, an epitope (anitbodies), a hapten, or a ligand, that allows the binding entity to bond or react covalently or non-covalently with a common function group on the surface of the substrate. Specific binding entities include, but are not limited to: deoxyribonucleic acids (DNA), ribonucleic acids (RNA), synthetic oligonucleoides, antibodies, proteins, peptides, lectins, modified polysaccarides, synthetic composite macromolecules, functionalized nanostructures, synthetic polymers, modified/blocked nucleotides/nucelosides, modified/blocked amino acids, fluorophores, chromophores, ligands, chelates, and haptens. In multiplexed embodiments, each microspot within an array of the sensor may have a different bio- or chemo-responsive layer specifically formulated to react with a particular biological or chemical analyte/target. For some embodiments, a further biological preparation of the surface may include applying non-specific binding blocking agents, etc.
One requirement for high-specificity identification of pathogens is the availability of probes (e.g., antibodies, proteins, immuno-receptors, etc.) that show a large binding affinity for the target. Often, antibodies specific to a pathogen are utilized, since they provide a high degree of specificity. The probe may be selected according to their specificity for certain functionalism. For example, the probes may include antibodies against various different surface-marker molecules of a particular pathogen, such as the four or five different antibodies that can bind with these kinds of functionality of anthrax. Sometimes, however, production of such materials is often difficult. For instance, antibodies may be hard to produce and purify, and a different probe must be substituted. Other examples of pathogen targets that are more available and just as specific in their capture of pathogens as antibodies may include gangliosides, which are sugar/lipid complexes targeted by many toxins (including anthrax).
Recently, immobilization of gangliosides on surfaces for binding assays have been demonstrated (Fang et al., “Ganglioside Microarrays for Toxin Detection,” Langmuir 2003, 19, 1500-1505). Details for detecting toxins using an array of biological membrane are also provided in U.S. Provisional Patent Application No. 60/392,275, which is incorporated herein by reference. For binding assays, gangliosides can be immobilized on surfaces of an evanescent sensor prior to deployment of the sensor. As an added bonus, the use of such binding reactions can result in greater specificity (fewer false positives) than most absorption spectrum-based standoff detection techniques. Alternatively, the sensing or responsive layer may include a polymer matrix, biomembranes with a ligand-gated ion channel, or chemical compounds may be used for detecting chemical toxins.
Once the sensor surface is prepared, the sensor is essentially ready for airborne pathogen detection, as shown in
The sensor system according to the present invention can exhibit improved degrees of sensitivity and specificity. According to the invention, the sensor is able to detect the presence of microbes (e.g., virus or bacteria) in a sample at levels of at least about 1 organism per liter, biological toxins present in a sample at levels of at least about 1 or 10 femtomoles per liter, and chemical toxins at levels of about 50-100 attomoles per liter. Furthermore, these reactions can be monitored in real-time, permitting their use in unmanned aerial vehicles, mobile equipment on the ground, and locality- or community-wide response networks.
Evanescent-field sensing generally monitors a change in optical phase. Numerous optical devices incorporate phase detection. Some of examples of these may include a resonant ring, a Mach Zehnder interferometer, or a Hartman interferometer. The sensor may take a variety of other forms, including a patterned optical circuit. The sensor, according to certain embodiments, is a waveguiding structure formed by a waveguiding containment layer, film, or effective index region located over or against a substrate. Preferably, the waveguiding region has a refractive index of at least 0.1% higher than the refractive index of the substrate. A diffraction grating may be contained in the waveguiding structure. A bio- or chemo-responsive layer is deposited adjacent to the waveguiding body or film, wherein the bio- or chemo-responsive layer is capable of interacting with the toxins of interest. The sensor may be fashioned from a substrate coated with a metallic film capable of supporting surface plasmon modes. In another embodiment, the sensor may be a substrate coated with multiple dielectric layers. The dielectric layers have varying optical indices, and the optical field has an evanescent tail extending beyond the layer immediately in contact with a medium to be sensed.
B. System Design
The basic sensor system is fairly simple to understand. Evanescent-field sensors can be made in a variety of shapes and sizes, and with a variety of materials, including glass, dielectric materials, metals, metal oxides, as well as relatively inexpensive plastics. Ideally, many sensors should be packaged together to provide the ability to switch to new sensors as old ones become contaminated or the surface chemistry is rendered inactive through use. In view of these considerations, the present invention provides a continuously renewable substrate that incorporates numerous sensors. The optical monitoring beams would presumably interact with only a subset of all of microspots on the sensor substrate at any given time.
No practical embodiment of toxin sensing technology, however, would target only one specific toxin. For this reason, multiple sensors should be operable in a multiplexed format. This could involve simultaneous monitoring of a plurality of sensors, or simply a sequential detection of individual sensors. In order to accommodate multiplexing, the continuous substrate would preferably have groups of sensors arranged in which the number of sensors in each group is roughly equal or corresponds to the number of toxin species one would wish to detect. For instance, if one wishes to monitor five toxin species, the substrate may be configured to contain five (5) adjacent evanescent field sensors. If each sensor is in the form of a microspot of about 2 mm in diameter, for example, a resulting array of microspot sensors would be roughly 10 mm wide×2 mm long, repeated many times along the entire length of the continuous substrate. Alternatively, if spatial considerations do not permit placement of the desired number of multiplexed sensors in a single line on the substrate, one could organize arrays of sensors in groupings of a two-dimensional rectilinear matrix, with two or more parallel rows and columns. For example with respect to microspots of 2 mm in diameter, like above, on a 10-mm wide substrate, 15 different toxins could be monitored with a 3×5 array of microspot sensors.
According to certain embodiments of the system, the evanescent-field sensor may have a collection of substrates, each having one or more sensing regions that can be optically interrogated in series or in parallel. In an embodiment, the evanescent-field sensor has a continuous substrate with at least two or more contiguous sets of sensor arrays on the substrate surface, such that each array comprises a predetermined set of multiple regions for biological or chemical sensing. In each array of sensors, the bio- or chemo-responsive layers are specifically formulated to react with one or more particular biological or chemical analyte. The substrate has tensile strength and pliability and can be supplied from a dispensing device as a single unit in a continuous fashion. The substrate can be configured to a fraction of its fully extended length along its longest dimension without breaking, and can be retrieved from such configuration as a continuous body suitable for performing molecular interactive assays with said molecular targets. For instance, the substrate is an optically transparent (polymer) film of about 50 microns to about 2 mm thick. In other embodiments, discussed in detail below, the evanescent-field sensor may also take the form of a rotatable platform.
The pathogen can be introduced to the sensor in a variety of ways, including direct air flow as well as fluid capture/flow. Hence, fluid (gas, aerosol, or liquid) flow across the sensor is another component of any sensing system. Fluids could be introduced either with macro or micro-fluidic systems, and incorporate reagents for assays included in the instrument. An air sample delivery system may include air filtration systems combined with flow channels, monitors, or even pathogen concentrating technology. An embodiment may have a network of channels made up of a number of different macro or microstructures, which may encourage efficient mixing of an air sample or vary the velocity of air sample flow by changing the dimensions of the channels.
In other embodiments, the air sample outlet may be redirected temporarily back through the sensing region to enable potential continuous circulation of the same air sample for a certain prescribed period of time before the sample is discharged from the system. This may allow better sampling of the contents in the air. The entire sensor system may be engineered to fit within a compact, mobile housing design.
An embodiment for a replaceable filter may be in the form of a replaceable cartridge. A cartridge design also has the advantage of being configurable to specific uses, such that different filter sizes can be implemented depending on the desired application. In the cartridge, the filter may be wound into a continuous roll. Analogous to the sensing regions on a sensor substrate, after certain period of time or when it become necessary, the filter roll can be mechanically advanced forward a fixed length to expose a new filter surface. A continuous roll of filters, limited only by the size of the filter roll and level of contamination present in the local environment, can provide a more efficient filtration process. Hence, the instrument can be deployed in the field for a longer interval of time without the need to change the filter or provide other maintenance.
One of the most important components of the sensor system is an optical interrogation apparatus for monitoring said chemo-responsive layer. The sensor is monitored by an optical beam, as shown in either
This geometry demonstrates the ability to utilize a diffractive optic to multiplex several sensors without many additional optics. Data relating to detection of biological or chemical targets obtained with this instrument is detailed below.
Other designs for the system are depicted as schematic representations in
Having described the general concept of the present invention, the following describes examples of possible embodiment. These detailed examples, however, are only some of the many possibilities for a sensor substrate design according to the present invention.
A. Grating Coupled Waveguide (GCW) Sensor
GCW sensors are excellent examples of evanescent field technology. While some features may be unique to GCW devices, this invention pertains to any evanescent-based biological sensors, where an evanescent optical field responds to biological events. Therefore, the sensor could have a transparent optical waveguide with grating or prism coupling (as above), metallic layers that exhibit surface plasmon modes, or even dielectric stacks that confine the optical field with total internal reflection. In any case, the general embodiment involves the monitoring of the optical mode as its evanescent tail responds to the biological stimulus. Optical sensor for selective detection of substances and/or for the detection of refractive index changes in gaseous, liquid, solid and porous samples. One may gain a fuller understand of specific details of the present invention in examples of similar GCW sensor devices, such as described in U.S. Pat. Nos. 4,815,843, 5,071,248, 5,738,825, or 6,455,004, to Tiefenthaler, et al., the contents of which are incorporated herein by reference.
An example of a GCW design may involve a plastic substrate, where the substrate index ns=1.53, the grating pitch Λ=538 nm, the grating thickness is tg=10 nm, the waveguide index nf=2.01, the waveguide thickness tf=110 nm, and the superstrate index is nominally the index of water (the solvent in which most experiments are performed, nc≧1.33). These numbers are of course only nominal values, since larger ranges of these parameters still satisfy the requirements for proper sensing operation. For instance, the grating pitch can range from about 300 nm to 5000 nm or more, depending upon the desired wavelength of operation and target device sensitivity. The substrate and waveguide indices can range from about 1.0 (air) to about 3.5 or greater depending upon the materials chosen. In order to provide optical confinement however, the substrate index is usually lower than the index of the confinement layer. The waveguide thickness is typically less than the operating wavelength in order to maintain a single confined mode for sensing.
The physical operation of GCW devices can be understood as an interaction between a free-space light field and the device's waveguide modes. This interaction is made possible by the diffraction grating, designed to diffract light of specific wavelengths at specific angles to their incoming propagation vectors. In a GCW device, like in
where βg is the waveguide propagation constant, βx is the free-space propagation constant, and Λ is the grating period. The same grating that couples this particular wavelength into the grating will also serve to couple this light back out of the waveguide, according to the same diffraction angle laws that governed the input coupling. The net result is the angular redirection of a narrow wavelength band of light incident on the GCW device; this narrow-band response is often referred to as a Wood anomaly. The design of the device determines the input angle and wavelength for waveguide coupling, as well as the output angle. This type of functionality is analogous to directional optical filtration, with obvious applications wherever optical filters are needed.
To maintain simplicity and efficiency of operation, the devices employed for biosensing are usually designed such that only the zeroth diffracted orders of the grating propagate in free space. The higher diffraction orders are avoided by designing a sub-wavelength grating, i.e., grating pitch is smaller than the desired operating wavelength. In such a situation, the coupling efficiency between the input/output light and the waveguide mode is large since higher orders do not remove power from the system. Moreover, since only the zeroth reflected and transmitted beams exist in free space, the GCW can thereby produce nearly total reflection or transmission of the desired (anomalous) wavelength.
An ability to tune the location (in both wavelength and angle) of the above resonance with the index of refraction of the waveguide superstrate has led to the use of GCW devices for biosensing applications. The evanescent tail of the propagating waveguide mode senses the superstrate index changes, thereby altering the guided mode's effective index. This changes the resonance condition of the GCW according to equation (1) above, and the resonance thus shifts to a new wavelength or angle location. The relationship between angle and wavelength is displayed in
B. Film-Based Substrates
The availability of small-volume sensors allows novel designs for compact, renewable biological pathogen or toxin systems. Individual polymeric sensors may be fabricated on flexible substrate. A portion of the substrate, having two arbitrarily designated ends, may be bent along its longest dimension into an arc or sinusoidal configuration, wherein one end touches or nearly touches the other, without breaking or inflicting irrevocable physical damage to the substrate. For instance, an individual sensor substrate may be made to measure 9 mm2×1 mm thick. Polymeric films of about 50 μm to about 1 or 2 mm thickness could instead be made, reducing the total sensor volume to only 1.35 mm3. This technology is ideally suited for military or civil defense and security applications, where miniaturization and mobility are critical concerns.
In particular embodiments, polymer film-based GCW sensors could be made compatible with mechanized commercial 35-mm film. Such a solution can take advantage of immediately available commercial technology from the film industry. For instance, a sensing region, according to such an embodiment, may be thought of as being analogous or equivalent to the surface of a frame of film. Film reels, sprockets, drive motors and other devices or mechanics of cameras or motion picture projectors can be adapted to advance each sensing region like a frame of film. Moreover, this approach would produce a renewable sensor surface, where a continuous roll provides new sensors that advance when the prior sensing surface is spent.
As an example, films of about 50-150 or 200 μm thick with embedded GCW sensors may be wound into a continuous roll. This embodiment is depicted in
C. Rotative Substrates
Film rolls are not the only possible embodiment of this invention, since the sensors could be deployed in virtually any arrangement. Other embodiments may include, but are not limited to, rotating platforms (e.g., disc, such as CD-ROM/DVD style formats) or carousel, or multi-sensor cartridges, etc, such as depicted in
As discussed above, one should be able to detect multiple toxins simultaneously in one instrument. Both film and rotative embodiments herein are equally applicable in this respect, because of the relatively small footprint of typical sensors (e.g., 9 mm2). With several sensing regions arranged in proximity on the film, as depicted in
Sensors could be pre-fabricated in disposable cartridges containing one or more film or CD substrates, according to such embodiments, allowing easy maintenance of deployed sensing systems. A replacement or second cartridge may be inserted into place when all of the sensors on a first cartridge have been expended; thereby, ensuring a series of new sensors for prolonged continuous monitoring.
The present evanescent-field sensor system may be applied to numerous uses for assaying a variety of biological or chemical molecules.
One of the most basic demonstrations of evanescent sensor technology is the monitoring of the sensor response as chemicals with different refractive indices are flowed across the sensor surface.
As an example of biological reaction with a sensor surface,
Taking advantage of recently developed technology (Fang et al., “Ganglioside Microarrays for Toxin Detection,” Langmuir 2003, 19, 1500-1505; U.S. Provisional Patent Application No. 60/392,275; and U.S. Patent Application Publication No. US2002/0094544 A1), arrays of micrometer-sized spots containing gangliosides may be fabricated within sensor regions. Ganglioside microarrays are robust, retaining their biological function and remaining associated with the substrate when drawn through an air/fluid interface. A different ganglioside compound (specific to a unique pathogen) may be immobilized on each separate sensor region of a substrate for simultaneous multi-pathogen detection according to the invention.
An electrostatic multilayer experiment may be performed also on a GCW sensor with incorporated fluidics. Since PSS (polystyrene sulfonate) and PAH (polyallyamine hydrochloride), each of which is of an opposite electrostatic charge, form well-defined monolayers (˜4 nm each), one can test quantitatively the surface sensitivity and dynamic range of the sensor itself.
The present invention has been described in general and in detail by way of examples. Persons skilled in the art understand that the invention is not limited necessarily to the specific embodiments disclosed. Modifications and variations may be made without departing from the scope of the invention as defined by the following claims or their equivalents, including equivalent components presently known, or to be developed, which may be used within the scope of the present invention. Hence, unless changes otherwise depart from the scope of the invention, the changes should be construed as being included herein.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US4815843||May 29, 1986||Mar 28, 1989||Oerlikon-Buhrle Holding Ag||Optical sensor for selective detection of substances and/or for the detection of refractive index changes in gaseous, liquid, solid and porous samples|
|US5071248||Nov 14, 1988||Dec 10, 1991||Asi Ag||Optical sensor for selective detection of substances and/or for the detection of refractive index changes in gaseous, liquid, solid and porous samples|
|US5804384||Dec 6, 1996||Sep 8, 1998||Vysis, Inc.||Devices and methods for detecting multiple analytes in samples|
|US5965456 *||Apr 29, 1997||Oct 12, 1999||Biacore Ab||Analyte detection|
|US6192168 *||Apr 9, 1999||Feb 20, 2001||The United States Of America As Represented By The Secretary Of The Navy||Reflectively coated optical waveguide and fluidics cell integration|
|US6242267||Mar 19, 1997||Jun 5, 2001||University Of Utah Research Foundation||Oscillation apparatus and methods for multi-analyte homogeneous fluoro-immunoassays|
|US6277628||Oct 2, 1998||Aug 21, 2001||Incyte Genomics, Inc.||Linear microarrays|
|US6455004||Sep 10, 1998||Sep 24, 2002||Kurt Tiefenthaler||Optical sensor and optical method for characterizing a chemical or biological substance|
|US20020127565||Aug 15, 2001||Sep 12, 2002||Sru Biosystems, Llc||Label-free high-throughput optical technique for detecting biomolecular interactions|
|US20020168295||Aug 15, 2001||Nov 14, 2002||Brian Cunningham||Label-free high-throughput optical technique for detecting biomolecular interactions|
|US20030017580||Jul 15, 2002||Jan 23, 2003||Sru Biosystems, Llc||Method for producing a colorimetric resonant reflection biosensor on rigid surfaces|
|US20030017581||Jul 23, 2002||Jan 23, 2003||Sru Biosystems, Llc||Method and machine for replicating holographic gratings on a substrate|
|US20030026891||Jul 23, 2002||Feb 6, 2003||Sru Biosystems, Llc||Method of making a plastic colorimetric resonant biosensor device with liquid handling capabilities|
|US20030027327||Jan 28, 2002||Feb 6, 2003||Sru Biosystems, Llc||Optical detection of label-free biomolecular interactions using microreplicated plastic sensor elements|
|US20030027328||Jan 28, 2002||Feb 6, 2003||Sru Biosystems, Llc||Guided mode resonant filter biosensor using a linear grating surface structure|
|US20030032039||Jun 26, 2002||Feb 13, 2003||Sru Biosystems, Llc||Method and apparatus for detecting biomolecular interactions|
|US20030059855||Jun 26, 2002||Mar 27, 2003||Sru Biosystems, Llc||Method and instrument for detecting biomolecular interactions|
|US20030068657||Sep 9, 2002||Apr 10, 2003||Sru Biosystems Llc||Label-free methods for performing assays using a colorimetric resonant reflectance optical biosensor|
|US20030077380||Oct 18, 2001||Apr 24, 2003||Lefkowitz Steven M.||Chemical arrays|
|US20030077660||Sep 25, 2002||Apr 24, 2003||Sru Biosystems, Llc||Method and apparatus for biosensor spectral shift detection|
|US20030092075||Sep 3, 2002||May 15, 2003||Sru Biosystems, Llc||Aldehyde chemical surface activation processes and test methods for colorimetric resonant sensors|
|US20030113766||Aug 26, 2002||Jun 19, 2003||Sru Biosystems, Llc||Amine activated colorimetric resonant biosensor|
|US20040132172||Jan 20, 2004||Jul 8, 2004||Brian Cunningham||Label-free high-throughput optical technique for detecting biomolecular interactions|
|US20040132214||Sep 22, 2003||Jul 8, 2004||Sru Biosystems, Llc||Label-free methods for performing assays using a colorimetric resonant optical biosensor|
|US20040151626||Oct 23, 2001||Aug 5, 2004||Brian Cunningham||Label-free high-throughput optical technique for detecting biomolecular interactions|
|US20040223881||May 8, 2003||Nov 11, 2004||Sru Biosystems||Detection of biochemical interactions on a biosensor using tunable filters and tunable lasers|
|WO2000040334A1||Jan 7, 2000||Jul 13, 2000||Pe Corporation (Ny)||Fiber array for contacting chemical species and methods for using and making same|
|WO2001071316A2||Mar 13, 2001||Sep 27, 2001||Wisys Technology Foundation, Inc.||One-dimensional arrays on optical fibers|
|WO2001071322A2||Mar 22, 2001||Sep 27, 2001||Goh M Cynthia||Method and apparatus for multiple-analyte assay|
|1||D. Stratis-Cullum et al., "A Miniature Biochip System for Detection of Aerosolized Bacillus globigii Spores", Anal. Chem. 2003, vol. 75, pp. 275-280.|
|2||G. Voirin et al., "High-Sensitivity Label-Free Detection of Small Molecules", CSEM Scientific and Technical Report 2001, p. 54.|
|3||M. Wiki et al., "Wavelength-interrogated optical sensor for biochemical applications", Optics Letters, vol. 25, No. 7, Apr. 1, 2000, pp. 463-465.|
|4||R. Horváth et al., "Optical Waveguide Sensor for On-Line Monitoring of Bacteria", Optics Letters, Jul. 15, 2003, vol. 28, No. 14, pp. 1233-1235.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7784678||Apr 14, 2009||Aug 31, 2010||Actherm Inc.||Analytical strip reading apparatus with a removable firmware device|
|US8046175||Jan 8, 2009||Oct 25, 2011||Actherm Inc||Analytical strip reading apparatus and the analyical strip used therein|
|US8300993||Nov 12, 2009||Oct 30, 2012||Mbio Diagnostics, Inc.||Waveguide with integrated lens|
|US8331751||Nov 9, 2010||Dec 11, 2012||mBio Diagnositcs, Inc.||Planar optical waveguide with core of low-index-of-refraction interrogation medium|
|US8489015 *||Nov 8, 2011||Jul 16, 2013||Wireless Expressways Inc.||Waveguide-based wireless distribution system and method of operation|
|US8586347||Sep 15, 2011||Nov 19, 2013||Mbio Diagnostics, Inc.||System and method for detecting multiple molecules in one assay|
|US8606066||Dec 4, 2012||Dec 10, 2013||Mbio Diagnostics, Inc.||Planar optical waveguide with core of low-index-of-refraction interrogation medium|
|US8796012||Dec 2, 2009||Aug 5, 2014||National Research Council Of Canada||Grating-based evanescent field molecular sensor using a thin silicon waveguide layer|
|US8897695||Jun 14, 2013||Nov 25, 2014||Wireless Expressways Inc.||Waveguide-based wireless distribution system and method of operation|
|US9212995||Mar 15, 2013||Dec 15, 2015||Mbio Diagnostics, Inc.||System and method for detecting multiple molecules in one assay|
|US9242248 *||Feb 11, 2013||Jan 26, 2016||The University Of North Carolina At Charlotte||Methods and devices for optical sorting of microspheres based on their resonant optical properties|
|US20090034902 *||Jan 5, 2007||Feb 5, 2009||Siemens Healthcare Diagnostics Inc.||Method for Increasing Signal Intensity in An Optical Waveguide Sensor|
|US20100094564 *||Jan 8, 2009||Apr 15, 2010||Chien-Chih Kuo||Analytical strip reading apparatus and the analyical strip used therein|
|US20100140341 *||Apr 14, 2009||Jun 10, 2010||Chien-Chih Kuo||Analytical strip reading apparatus with a removable firmware device|
|US20110049388 *||Nov 9, 2010||Mar 3, 2011||Mbio Diagnostics, Inc.||Planar optical waveguide with core of low-index-of-refraction interrogation medium|
|US20110223688 *||Dec 2, 2009||Sep 15, 2011||Bill Sinclair||Grating-based evanescent field molecular sensor using a thin silicon waveguide layer|
|US20140069850 *||Feb 11, 2013||Mar 13, 2014||University Of North Carolina At Charlotte||Methods and devices for optical sorting of microspheres based on their resonant optical properties|
|WO2010063116A1 *||Dec 2, 2009||Jun 10, 2010||National Research Council Of Canada||Grating-based evanescent field molecular sensor using a thin silicon waveguide layer|
|U.S. Classification||435/287.2, 436/805, 422/82.05, 436/525, 436/524, 385/30, 435/5, 385/12, 436/527, 435/808, 422/82.11, 436/529, 436/528, 435/287.9, 435/288.7, 436/514, 435/6.12|
|International Classification||C12M1/34, G01N33/543, C12M1/26|
|Cooperative Classification||Y10S435/808, Y10S436/805, G01N33/54373|
|European Classification||G01N33/543K2, C12M1/26B|
|Mar 5, 2004||AS||Assignment|
Owner name: CORNING INCORPORATED, NEW YORK
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:MOZDY, ERIC J.;QUAN, FREDERIC J-Y;YUEN, POKI;REEL/FRAME:015055/0646;SIGNING DATES FROM 20030717 TO 20040305
|Mar 17, 2009||CC||Certificate of correction|
|Nov 7, 2011||FPAY||Fee payment|
Year of fee payment: 4
|Dec 18, 2015||REMI||Maintenance fee reminder mailed|
|May 6, 2016||LAPS||Lapse for failure to pay maintenance fees|
|Jun 28, 2016||FP||Expired due to failure to pay maintenance fee|
Effective date: 20160506